System and method for non-invasive glucose monitoring using near infrared spectroscopy

ABSTRACT

Current glucose meters provide instantaneous results however are invasive and painful thus causing reduced compliance. A non-invasive, portable, wearable device would be ideal for monitoring and recording and provide a distinct advantage to current glucose monitors.

FIELD OF THE INVENTION

This invention relates to a method of monitoring of diabetes, more specifically it relates to blood glucose monitoring. It also relates to the apparatus used in the method. The principle of the invention can also be sued to monitor other substances circulating in the blood, such as glycolated hemoglobin and cholesterol.

BACKGROUND OF THE INVENTION

Diabetes mellitus is a chronic disease currently affecting about one third of the US population including those in the pre diabetic stage. Clinical management of both Type-1 and Type-2 diabetes relies on accurate monitoring of blood glucose concentrations at least once a day. Current devices rely on enzyme oxidation analyses, which require a prick of blood every time glucose levels are checked. This invasive method of glucose monitoring causes pain and tissue-sensitivity to users making it difficult to have repeated measurements causing failure in compliance, especially for chronic patients.

26 million people in the US are affected by diabetes while 79 million in the pre-diabetic stage. Worldwide, the number swells to 285 million adults. Further, 3.8 million deaths are caused by diabetes related diseases in the world annually. Patients who are required to use traditional glucose monitoring methods are often faced with pain and increased sensitivity in their fingertips.

SUMMARY OF THE INVENTION

The present invention relates to techniques for non-invasive blood glucose measurements via imaging. It is based on the observation that there is a distinction between the substance to be measured and water that can be measured via multispectral near-infrared spectroscopy (NIR). Thus, the present invention allows for an initial absorption measurement at a continuous or relatively high sampling rate at discrete wavelengths somewhere within the range of 600 nm to about 1000 nm over a sufficient period of time so as to be able to analyze any temporal variations while also providing time tag information for systolic and diastolic events. This information along with pulse oximetry information taken at this time is used to help estimate actual blood concentration. After this initial absorption data information has been taken another round of absorption data is taken at a lower sampling rate utilizing at least one wavelength within the about 600 nm to about 1000 nm range. This raw data is collected at least at the time tag points related to systolic and diastolic events, but greater collection of data points is also embraced. This raw data is corrected via a convolution function while also utilizing a Monte Carlo simulation and, along with pulse oximetry information, a mixing model equation to provide initial estimate of blood concentration. The estimate is further optimized by genetic algorithm for a final blood substance reading.

The invention also relates to an apparatus specifically designed to carry out the method of the invention. The apparatus includes a means of illuminating a place on a patient's body where the measurement can be made and a means for measuring the amount of absorption of the illumination. The apparatus also includes a means for the data to be recorded and analyzed and then transformed into a meaningful result. The apparatus further includes a means to report its results as well as a communication ability to other devices.

BRIEF DESCRIPTION OF THE DRAWINGS

So that those having ordinary skill in the art will have a better understanding of how to make and use the disclosed gel blends, reference is made to the accompanying figures wherein:

FIGS. 1A-1F show spectra comparisons for glucose and water;

FIG. 2 illustrates a skin phantom for transillumination imaging;

FIG. 3 displays cross-section of a skin phantom showing location of capillary tubes;

FIG. 4A illustrates an experimental set-up for Monte Carlo simulation;

FIG. 4B illustrates a corrected transillumination imaging apparatus;

FIG. 5 shows intensity to μ_(a) relation performance when applying Beer's Law;

FIG. 6 shows intensity to μ_(a) relation performance when applying μ_(eff) equation;

FIG. 7 shows intensity to μ_(a) relation performance when applying nevoscope corrected equation;

FIG. 8 shows a schematic of one embodiment of the present invention as it optimizes the system utilizing genetic algorithm;

FIG. 9 demonstrates the transmission simulation images of melanin, blood, and glucose;

FIG. 10 depicts an estimation of un-mixing results;

FIG. 11 displays schematically one embodiment of the present invention;

FIG. 12 illustrates shows a single-source (multiplexed)-co-ax receiver;

FIG. 13 depicts system level configuration of one embodiment of the present invention;

FIGS. 14A-14C show simulated versus tube phantom; and

FIGS. 15A-15H show absorption measurements across the simulated phantom and imaged physical tube phantom for various levels of glucose concentration at different wavelengths.

DETAILED DESCRIPTION OF INVENTION

The following is a detailed description of the invention provided to aid those skilled in the art in practicing the present invention. Those of ordinary skill in the art may make modifications and variations in the embodiments described herein without departing from the spirit or scope of the present invention. Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. The terminology used in the description of the invention herein is for describing particular embodiments only and is not intended to be limiting of the invention. All publications, patent applications, patents, figures and other references mentioned herein are expressly incorporated by reference in their entirety.

More particularly, the invention relates to a method of monitoring blood concentration of a substance which comprises measuring a initial absorption data using near infrared spectroscopy (NIR), obtaining a second set of absorption data, adjusting the data using a convolution function and a Monte Carlo simulation, and using a mixing model equation along with pulse oximetry information and the adjusted data to provide an initial estimate of the level of the desired substance.

In a particular embodiment of the invention, the method is non-invasive to a patient whose blood is being analyzed.

The substance to be measured can be any substance which has an observable difference with water at the wavelengths at which the measurements are taken. Non-limiting examples include glucose, glycolated hemoglobin or cholesterol.

The initial absorption is measured over a sufficient period of time to analyze possible temporal variations while also providing time tag information for systolic and diastolic events. The initial estimate of the level of the desired substance is optimized by genetic algorithm to obtain a final blood reading.

Another embodiment of the invention relates to a method of monitoring blood concentration of glucose which comprises measuring a initial absorption data using near infrared spectroscopy (NIR), obtaining a second set of absorption data, adjusting the data using a convolution function and a Monte Carlo simulation, using a mixing model equation along with pulse oximetry information and the adjusted data to provide an initial estimate of the level of glucose.

Another embodiment of the invention relates to a method as described above which is non-invasive to a patient whose blood is being analyzed. The initial absorption can be measured over a sufficient period of time to analyze possible temporal variations while also providing time tag information for systolic and diastolic events. The initial estimate of the level of glucose can be optimized by genetic algorithm to obtain a final blood glucose reading.

Yet another embodiment of the invention relates to an apparatus for obtaining a non-invasive measurement of a substance in the blood which comprises, a NIR light source, a detector to determine absorption, a computer to analyze and transform data a power source, an archive, a communication system , and a user interface. In some embodiments the apparatus has at least one component of the apparatus can be placed on the skin. A non-limiting example is the ear lobe.

In certain embodiments of the present invention illumination is carried out in the optical and NIR range of about 600 nm- about 1200 nm. In certain embodiments of the present invention pulse mode measurement can be utilized wherein instead of collecting data at regular sampling rate, the data can be collected at specific times related to desired events and/or averaged out over a time period. For example, the absorption data can be first collected at 600 and 910 nm to measure heart rate and related events such systolic and diastolic events at higher sampling rates. Once the heart rate events are established, subsequent data is collected at these time intervals through appropriate programming of the sample, hold and analog-to-digital convertor of the data acquisition system/chip.

In certain embodiments of the present invention data is collected at specific times such as systolic and diastolic events of the heart cycle. The data acquisition system is synchronized with these events.

In certain embodiments of the present invent surface are of the tissue that is illuminated has an about 1 cm diameter maximum value. This refers to the surface area of the tissue that is illuminated by a source or multiples of sources that illuminates the tissue with specific visible optical and NIR beam(s) to produce images and measurements of absorption data from detectors using either transmittance or transillumination methods as defined above.

In certain embodiments of the present invention the glucose measurement range is about 3 mmol/L—about 10 mmol/L or about 50mg/dL- about 150mg/dL (calibrated with standard scale 50-500 pmol/L) with accuracy within 10%; and sensitivity >90%.

Certain embodiments of the present invention utilize a low-power consumption subsystem design.

Certain embodiments of the present invention utilize Li-Polymer battery with battery charging and power management.

Certain embodiments of the present invention utilize Micro-USB connectivity for battery charging.

In certain exemplary embodiments of the present invention blood glucose measurement takes place on any skin surface of individual. In a further embodiment the present invention is affixed to the ear lobe to effectuate the measurements.

In certain exemplary embodiments of the present invention the measurement device of the interacts wirelessly with a receiving device to receive and record measurements and interface with patient and/or care provider. The list of wireless devices includes but is not limited to, smart phone devices, laptop computers, tablets, and stand alone wireless device developed solely for the present invention.

Certain embodiments of the present invention utilize system integration with standard components such as data sampling/acquisition chips with signal multiplexers and analog to digital converters, and portable processors/computers as well as control and processing/estimation algorithms on portable processors/computers.

Certain embodiments of the present invention perform local computation and processing as well as storage and wireless communication/networking via applications for smart phone or computing device.

Early work related to the present invention stems from finding a distinction between glucose and water that could be measured via multispectral near-infrared spectroscopy (NIR). In order to begin addressing this, spectra of water and glucose solutions were taken using an optical spectrum analyzer. Using the data from the spectrum, specific wavelengths were targeted for the analysis of absorption coefficients at respective wavelengths. Preliminary data confirms that this method is viable as absorption coefficients vs. wavelength in the NIR show a significant distinction (FIGS. 1A-1F). Further mathematical analysis of the optical properties of skin yields:

${\mu_{a}^{baseline}(\lambda)} = {0.244 + {85.3{e^{\frac{- {({\lambda - 154})}}{66.2}}\left\lbrack {cm}^{- 1} \right\rbrack}}}$ μ_(a)^(melanin)(λ) = 6.6 × 10¹¹(λ^(−3.33)) μ_(a)^(epidermis)(λ) = C^(melanin)μ_(a)^(melanin)(λ) + (1 − C^(melanin))μ_(a)^(baseline)(λ) μ_(a)^(dermis)(λ) = C^(blood)μ_(a)^(blood)(λ) + (1 − C^(blood))μ_(a)^(baseline)(λ) μ_(a)^(blood)(λ) = ([SO₂])μ_(a)^(HbO₂)(λ) + (1 − [SO₂])μ_(a)^(Hb)(λ)

where

-   -   μ_(a) (absorption coefficient)     -   μ_(s) (scattering coefficient)     -   g (anisotropy factor)     -   n (refraction index) .

These equations are modeled for measurements of absorption coefficients related to specific chromophores such as (deoxy)hemoglobin (H_(b)), oxygenated hemoglobin (H_(b)O₂) in the blood in a tissue that is imaged through a direct transmittance or a transillumination method. In a direct transmittance method, the tissue is illuminated by a visible light or NIR source at specific wavelength(s) in the perpendicular direction to the surface of the tissue from one side, transmitted through the tissue, and collected on the other side by a single and/or a plurality of detectors that measure the intensity of the transmitted beam to determine absorption data at the specific location of the tissue. The location is specified by a pixel in the overall image that is produced by repeating the above process at different locations (pixels) for further processing and analysis to estimate concentration of specific chromophores in the tissue. Certain embodiments of the present invention utilize the direct transmittance method.

In a further mode of illumination referred to herein as transillumination, the visible light and NIR beam at specific wavelength(s) is directed at about an 45 degree angle to the surface of the tissue and a backscattered diffused beam is collected by the detectors on the same side of the tissue to form the image. Certain embodiments of the present invention utilize the transillumination method.

Transillumination and direct transmittance are not the only illumination methods embraced by the present invention and are discussed for illustrative purposes only. Any other illumination process that is known to one skilled in the art is embraced by the present invention.

For illustrative purposes only, transillumination absorption tests are often done with an illumination ring placed over a skin phantom (FIG. 2), however any other standard transillumination protocol known to one skilled in the art is embraced by the present invention.

One example of a transillumination test utilizes a particular phantom with 5 embedded capillary tubes spaced at 0.5 mm depth increments and the tubes can be filled with artificial HbO₂ or Hb (FIG. 3). Transillumination imaging for the example can be seen in FIGS. 4A and 4B. For each simulation utilizing this example a random position in the ring is selected for entrance to voxel grid at 45 degree angle as seen in FIG. 4A and 4B described by:

$x = {\sqrt{{\left( {r_{2}^{2} - r_{1}^{2}} \right)\xi_{1}} + r_{1}^{2}}{\cos \left( {2{\pi\xi}_{2}} \right)}}$ $y = {\sqrt{{\left( {r_{2}^{2} - r_{1}^{2}} \right)\xi_{1}} + r_{1}^{2}}{\sin \left( {2{\pi\xi}_{2}} \right)}}$ ${dx} = {{- \frac{\sqrt{2}}{2}}{\cos \left( {2{\pi\xi}_{2}} \right)}}$ ${dy} - {\frac{\sqrt{2}}{2}{\sin \left( {2{\pi\xi}_{2}} \right)}}$ ${dz} = \frac{\sqrt{2}}{2}$

Intensity to absorption coefficient μ_(a)relation is modeled for chromophore separation through the inverse equation

μ_(a) =f ⁻¹ (l, I/I₀)

Where I is a pixel intensity value in an image of the tissue with the chromophore such as oxygen or glucose, I₀ is the intensity from the tissue without the chromophore, μ_(a) is absorption coefficient of the chromophore, and l is the depth of the location of the chromophore in the tissue. The results of this chromophore correction test can be seen in FIGS. 5-8. Certain embodiments of the present invention use the measurement protocol described above to achieve glucose concentration measurements in the blood of test subjects.

In certain embodiments of the present invention, a Monte Carlo simulation of the tissue and imaging method is used in tandem with the multispectral NIR light. In one simulation utilizing a voxel-based forward imaging model of the embodiment the simulation voxel volume was 16×16×50 voxels which correlates to a physical size value of about 1.2 cm×1.2 cm x 0.5 cm (where chromophores were simulated up to the depth of 0.5 cm for a surface imaging area of 1.2 cm×1.2 cm). The number of voxels and dimensions can be varied and set with respect to physical dimensions of the sensor instrumentation and therefore can vary greatly in further embodiments of the present invention with respect to the example herein.

The embodiment was illuminated with a uniform square light source of about 1.2 cm×1.2 cm with a normal angle photon entry into the voxel volume. Illumination wavelengths utilized with respect to this exemplary embodiment included 600 nm, 680, nm, 780 nm, 800 nm, 875 nm, 910 nm and 980 nm. The embodiment also used a transmission detector of 100 pixels over 0.75 cm² with 100 million photons per wavelength. In further embodiments of the present invention the pixel size range can be from about 2 mm×2 mm to about 1 cm×1cm.

The pixel intensity in the transmission image is assumed dependent on the total absorption coefficient of the volume:

I/I ₀ =f(μ_(a))

In the embodiment, based on simulation at 780 nm, the relation equation may take the form:

I/I ₀=exp (−0.6316√{square root over (1.161 μ_(a) ²+9.503 μ_(a))})

In the embodiment a linear mixing model was assumed like so:

μ_(a)(λ)=C _(Mμ) _(a) ^(melanin) (λ)+C _(μ) _(a) ^(blood) (λ)+(1−C _(M) −C _(B))μ_(a) ^(baseline) (μ)

μ_(a) ^(blood) (μ)−[HbO₂]μ_(a) ^(HbO) ² (λ)+[Hb]μ_(a) ^(Hb) (λ)+[Glocose]μ_(a) ^(Glucose) (λ)

and μ_(a) ^(Glucose) (λ) is measured experimentally for a concentration of 1 mg/dL in water (Hence, a glucose concentration value for the embodiment of 100% would correspond to 1 mg/dL

Oxygen saturation:

$\left\lbrack {SO}_{2} \right\rbrack = \frac{\left\lbrack {HbO}_{2} \right\rbrack}{\left\lbrack {HbO}_{2} \right\rbrack + \lbrack{Hb}\rbrack}$

was assumed to be 75% for the embodiment. The melanin concentration (C_(M)), Blood concentration (C_(b)), and glucose concentration ([Glucose]) are left as unknown variables. (FIG. 10)

An estimation of glucose measurements in the simulated phantom using the volume model, substance true volume concentrations of melanin (1%), blood Hb (30%), oxygen saturation in HbO2 (75%), and glucose (100%) using the first wavelength set−1 as an example (embodiment) of 600, 680, 780, 800, 875 nm. The results are shown in FIG. 11. In the table, CM is the fraction volume for melanin (1%), CB is the fraction volume of total blood (Hb+HbO2), and Glucose is 100% with a regular concentration of 140 mg dL. The results of estimation of these substances in the simulated phantom using this set−1 are presented in the second column of the table as an example. The third shows the improvement in results using the preferred wavelength set−2 that includes 600 nm, 710 nm, 760 nm, 800 nm, 875 nm, 910nm and 980 nm that resulted in better estimation.

A simulated volume, with true parameters Cm=1% Cb=30% and [Glucose]=100%, was simulated by Monte Carlo simulation to produce a set of multispectral transmission images. The pixel values in these images were averaged to a single number. The average pixel intensity number was converted to an absorption coefficient value.

In one embodiment of the present invention a linear array of LEDs at wavelengths including 600 nm, 710, nm, 760 nm, 800 nm, 875 nm, 910 nm and 980 nm are utilized. In the embodiment illumination is completed with a small angle divergent beam or a regular collimated beam and there is alignment with spatially distributed sensors to detect diffused transmittance. The embodiment also embraces drivers and pre-amplifiers. The synchronized control data acquisition system of this embodiment can be stand alone, synchronized with pulse rate, and synchronized with external programmed mode. Data collected from detector while the source is illuminated can be synchronized at an adaptable sampling rate for the embodiment. That means that data can be collected at regular interval with a sampling rate of 1 Hz to 100 KHz depending on the data acquisition electronics and storage system, and the requirement of the data processing algorithm. For example, once the pulse rate through oximetry is determined, the data can be sampled at the heart rate including systolic and diastolic events to compare the increase of absorption in the increased blood volume between diastole and systole of the heart cycle.

In one embodiment of the present invention an optical device with a linear array or circular co-axial cable based module of multispectral LED sources aligned with sensors first demonstrates pulse oximetry to provide reference of pulse rate and relative oxygen level. In the embodiment the pulse rate is used to tag the measurements to estimate the increase in blood glucose with the increased volume of blood in the tissue. Sampled data is then analyzed through un-mixing model based analysis of multiple measurements taken at selected wavelengths during the diastole and systole of the heart cycle. FIG. 11 shows a systematic diagram of an embodiment of the system showing on left a subject wearing a linear source-detector array based sensor clip at the earlobe. In this embodiment, each source is tuned at a specific individual wavelength. The clip is shown in the black figure at the bottom where the earlobe is to be placed in the middle cavity. Major parts of the embodiment are shown on the right including the linear array source-detector based sensor system, a computer-chip processor used for data acquisition, sampling and analysis, and a smart mobile device to store and display the data and associated analysis for monitoring, diagnosis and therapeutic intervention purposes.

FIG. 12 shows an alternate embodiment of the co-axial sensor-detector array where a single source is modulated to provide different wavelength beams at sequential time-slots (on the left). Various co-axial detectors tuned at different wavelengths are circularly rotated and aligned to radiation beam for scanning the tissue for measurements.

In the embodiment the raw signals are processed through a convolution function representing the degradation of the signal caused by physical illuminators and sensor coupling response transfer functions. Once the initial estimate of oxygen is determined (using well-known pulse oximetry method, the glucose is estimated by solving the mixing model equation using the successive measurements taken at pulse rate (with diastole and systole time tags) for increased blood volume in the tissue. The optimization of glucose estimation from the mixing model can be performed using the known optimization methods such as genetic algorithms. While the initial glucose estimate from the above mixing equation provides a good “first guess”, the solution obtained may not be optimal and can be further improved through known optimization methods such as, but not limited to the genetic algorithm (GA) optimization method (L. Davis, Handbook of Genetic Algorithms. New York: Van Nostrand Reinhold, 1991)

The GA optimization begins by initializing a population of initial and candidate solutions. Each candidate solution is encoded as a “chromosome” for use during the GA. The chromosome for one particular individual in the population is defined by the melanin, blood, and glucose concentrations. For example, the chromosome for the initial volume estimate (henceforth known as the model chromosome) is defined as the set

{μ_(a) ^(melanin), μ_(a) ^(Hb), μ_(a) ^(HbO) ₂, μ_(a) ^(glucose)}

The values in each chromosome, known as alleles, represent the average concentration distributed in the tissue of the respective chromophores, melanin, hemoglobin, oxygenated hemoglobin (or total blood as the combined value) and glucose over the voxels for which data is collected for the embodiment. To further improve the estimation of distribution of chromophores over the imaged area (voxels), members of the GA population are varied around the model chromosome according to three concentric categories, circular areas around the center where the source and central detector pair is aligned. This is defined as red central space. The surrounding circular area of detector space shown in yellow belongs to second category and detector space in green represents the third category for weighting the illumination scattering effect or spread of beam in the tissue.

For the no bias category, the weights used in GA optimization are assigned from the Monet-Carlo simulation results. For example, in certain embodiments of the present invention they could be 50%, 30%, and 20%, respectively. For the shallow bias category of certain embodiments of the present invention, each allele has a 15% chance of decreasing by 10% (meaning the diffusion is stronger giving less weight to the data collected in central (red) zone), an 80% of not changing, and a 5% chance of increasing by 10% (meaning that diffusion is weaker to give more weight to the data collected in central detector space). The weights in remaining surrounding areas are adjusted accordingly for normalization to 100% total. For example it could change from 50-30-20 to 40-30-30 depending on the embodiment and conditions. Stronger or weaker biases could be created depending on the type of skin, e.g. stronger for darker (more amount of melanin) and weaker for lighter skin (less amount of melanin). In this manner, population variability is maintained, but each chromosome is based on the initial chromosome representing initial distribution obtained from the mixing equation solution.

GA requires formulation of a fitness function to evaluate the goodness of each possible solution based on the chromosome variations. Chromosomes are evaluated as to their fitness by executing the forward model on the chromosome (computing the distribution of absorption data using the estimated chromophore values in the Monte-Carlo model), and then comparing it with the real detector data acquired from the tissue for a particular embodiment of the present invention. The fitness F of each chromosome is then evaluated by a comparison between the multispectral images of the tissue (I_(λ) ^(real)) and the images generated by the forward model simulation (I_(λ)) on that chromosome, within the defined mask of bias category distribution as defined above:

$F = {- {\ln\left( {\frac{1}{N_{\lambda}N_{}}{\sum\limits_{\lambda,x,y,}{\frac{{{I_{\lambda}\left( {x,y} \right)} - {I_{\lambda}^{real}\left( {x,y} \right)}}}{I_{\lambda}^{real}\left( {x,y} \right)}{m\left( {x,y} \right)}}}} \right)}}$

where N_(λ) is the number of wavelengths used for imaging, and N_(l) is the number of data points within the mask such that N_(l)=Σ_(x,y)m(x,y).

For the embodiment the calibration is performed through a look table with respect to oximetry measurements that is normalized through ratiometric comparative measurements of pulse oximetry at 600 and 910 nm as it will remove the melanin and other absorption variables in the mixing model.

EXPERIMENTAL

The absorption per wave length was determined for 132 phantom samples and 132 simulated samples at various levels of glucose concentration at different wavelengths.

FIGS. 14A-14C show Simulation versus Tube Phantom. On the left is a simulated tissue image from Monte-Carlo simulation at the regular glucose level of 140 mg/dL; On the right are images of the physical tube-phantom taking from a multi-spectral CCD camera with no glucose and 100% glucose volume in the embedded tube in the middle for two example wavelengths: 680 nm and 875 nm.

The measurements shown in FIGS. 15A-15H are used in the glucose estimation using the described model.

Simulation Volume Model

-   10×10 pixels -   Transmission Detector: 10×10 pixels, for an overall physical     detector area of 0.75 cm2 Voxel volume: 16×16×50 voxels, of physical     size 1.2 cm×1.2 cm×0.5 cm -   2×16×2 voxel, of physical size 0.15 cm×16 cm×0.15 cm, tube embedded     in center of volume -   Illumination: A uniform square light source, 1.2 cm×1.2 cm (covering     the entire volume), with a perpendicular entry angle for photons. -   Wavelengths available: 600, 680, 780, 800, 875 nm -   100 million photos simulated per wavelength -   Melanin concentration=1% -   Blood concentration=30% -   SO2 concentration=75%

Glucose concentration = Experiment Danger Low 20 mg/dL Low 60 mg/dL Fasting 100 mg/dL Regular 140 mg/dL High 200 mg/dL Danger High 500 mg/dL

Linear mixing model assumed:

μ_(a) (λ)=C _(Mμ) _(a) ^(melanin) (λ)+C _(Bμ) _(a) ^(blood) (λ)+(1−C _(M) −C _(B))μ_(a) ^(baseline) (λ)

where

μ_(a) ^(blood) (λ)=[HbO₂]μ_(a) ^(HbO) ² (λ)+[Hb]μ_(a) ^(Hb) (λ)+[Glucose]μ_(a) ^(Glucose) (λ)

The are shown in FIG. 15.

Although the systems and methods of the present disclosure have been described with reference to exemplary embodiments thereof, the present disclosure is not limited thereby. Indeed, the exemplary embodiments are implementations of the disclosed systems and methods are provided for illustrative and non-limitative purposes. Changes, modifications, enhancements and/or refinements to the disclosed systems and methods may be made without departing from the spirit or scope of the present disclosure. Accordingly, such changes, modifications, enhancements and/or refinements are encompassed within the scope of the present invention. 

1. A method of monitoring blood concentration of a substance which comprises: a. measuring a initial absorption data using near infrared spectroscopy (NIR); b. obtaining a second set of absorption data; c. adjusting the data using a convolution function and a Monte Carlo simulation; d. using a mixing model equation along with pulse oximetry information and the adjusted data to provide an initial estimate of the level of the desired substance.
 2. The method of claim 1 which is non-invasive to a patient whose blood is being analyzed.
 3. The method of claim 1 wherein the substance is glucose, glycolated hemoglobin or cholesterol.
 4. The method of claim 1 wherein the initial absorption is measured over a sufficient period of time to analyze possible temporal variations while also providing time tag information for systolic and diastolic events.
 5. The method of claim 1 wherein the initial estimate of the level of the desired substance is optimized by genetic algorithm to obtain a final blood reading.
 6. A method of monitoring blood concentration of glucose which comprises: a. measuring a initial absorption data using near infrared spectroscopy (NIR); b. obtaining a second set of absorption data; c. adjusting the data using a convolution function and a Monte Carlo simulation; d. using a mixing model equation along with pulse oximetry information and the adjusted data to provide an initial estimate of the level of glucose.
 7. The method of claim 6 which is non-invasive to a patient whose blood is being analyzed.
 8. The method of claim 6 wherein the initial absorption is measured over a sufficient period of time to analyze possible temporal variations while also providing time tag information for systolic and diastolic events.
 9. The method of claim 6 wherein the initial estimate of the level of glucose is optimized by genetic algorithm to obtain a final blood glucose reading.
 10. An apparatus for obtaining a non-invasive measurement of a substance in the blood which comprises; a. a NIR light source; b. a detector to determine absorption; c. a computer to analyze and transform data; d. a power source; e. an archive; f. a communication system; and g. a user interface.
 11. The apparatus of claim 10 wherein at least one component of the apparatus can be placed on the skin.
 12. The apparatus of claim 11 wherein the apparatus can be placed on the ear lobe. 